Systems, devices and methods used in verifying neural stimulation capture

ABSTRACT

Various system embodiments comprise a neural stimulator, a premature ventricular contraction (PVC) event detector, a heart rate detector, an analyzer, and a controller. The neural stimulator is adapted to generate a stimulation signal adapted to stimulate an autonomic neural target. The analyzer is adapted to, in response to a PVC event signal from the PVC event detector, generate an autonomic balance indicator (ABI) as a function of pre-PVC heart rate data and post-PVC heart rate data. Other aspects and embodiments are provided herein.

CLAIM OF PRIORITY

This application is a continuation of and claims the benefit of priorityunder 35 U.S.C. §120 to U.S. patent application Ser. No. 13/273,436,filed on Oct. 14, 2011, which is a continuation of and claims thebenefit of priority under 35 U.S.C. §120 to U.S. patent application Ser.No. 13/024,120, filed on Feb. 9, 2011, now issued as U.S. Pat. No.8,041,423, which is a continuation of and claims the benefit of priorityunder 35 U.S.C. §120 to U.S. patent application Ser. No. 12/861,370,filed on Aug. 23, 2010, now issued as U.S. Pat. No. 7,894,895, which isa continuation of and claims the benefit of priority under 35 U.S.C.§120 to U.S. patent application Ser. No. 11/279,188, filed on Apr. 10,2006, now issued as U.S. Pat. No. 7,783,349, which are herebyincorporated by reference herein in their entirety.

CROSS REFERENCE TO RELATED APPLICATIONS

The following commonly assigned U.S. patent applications are related,and are herein incorporated by reference in their entirety: “AutomaticBaroreflex Modulation Based on Cardiac Activity,” Ser. No. 10/746,846,filed on Dec. 24, 2003, now abandoned; “System and Method ForClosed-Loop Neural Stimulation,” Ser. No. 11/280,940, filed on Nov. 16,2005, published as US 2006/0135998 A1; “System and Method ForClosed-Loop Neural Stimulation,” Ser. No. 10/992,319, filed on Nov. 18,2004, published as US 2006/0106.429 A1; and “Cardiac Rhythm ManagementDevice With Neural Sensor,” Ser. No. 10/992,320, filed on Nov. 18, 2004,now U.S. Pat. No. 7,769,450.

TECHNICAL FIELD

This application relates generally to neural stimulation systems and,more particularly, to systems, devices and methods for providingclosed-loop neural stimulation.

BACKGROUND

The automatic nervous system (ANS) regulates “involuntary” organs andmaintains normal internal function and works with the somatic nervoussystem. The ANS includes the sympathetic nervous system and theparasympathetic nervous system. The sympathetic nervous system isaffiliated with stress and the “fight or flight response” toemergencies, and the parasympathetic nervous system is affiliated withrelaxation and the “rest and digest response.” Autonomic balancereflects the relationship between parasympathetic and sympatheticactivity. Changes in autonomic balance are reflected in changes in heartrate, heart rhythm, contractility, remodeling, inflammation and bloodpressure. Changes in autonomic balance can also be seen in otherphysiological changes, such as changes in abdominal pain, appetite,stamina, emotions, personality, muscle tone, sleep, and allergies, forexample.

It is desirable to use a measurement of autonomic balance in order toappropriately control or titrate various neural stimulation therapies.Neural stimulators have been proposed to treat a variety of disorders,such as epilepsy, obesity, breathing disorders, hypertension, postmyocardial infarction (MI) remodeling and heart failure. Directelectrical stimulation has been applied to the carotid sinus and vagusnerve. Research has indicated that electrical stimulation of the carotidsinus nerve can result in reduction of experimental hypertension, andthat direct electrical stimulation to the pressoreceptive regions of thecarotid sinus itself brings about reflex reduction in experimentalhypertension. Electrical systems have been proposed to treathypertension in patients who do not otherwise respond to therapyinvolving lifestyle changes and hypertension drugs, and possibly toreduce drug dependency for other patients. The stimulation ofsympathetic afferents triggers sympathetic activation, parasympatheticinhibition, vasoconstriction, and tachycardia. In contrast,parasympathetic activation results in bradycardia, vasodilation andinhibition of vasopressin release. Direct stimulation of the vagalparasympathetic fibers has been shown to reduce heart rate. In addition,some research indicates that chronic stimulation of the vagus nerve maybe of protective myocardial benefit following cardiac ischemic insult.Reduced autonomic balance (increase in sympathetic and decrease inparasympathetic cardiac tone) during heart failure has been shown to beassociated with left ventricular dysfunction and increased mortality.Research also indicates that increasing parasympathetic tone andreducing sympathetic tone may protect the myocardium from furtherremodeling and predisposition to fatal arrhythmias following myocardialinfarction.

SUMMARY

Various aspects of the present subject matter relate to a system.Various system embodiments comprise a neural stimulator, a prematureventricular contraction (PVC) event detector, a heart rate detector, ananalyzer, and a controller. The neural stimulator is adapted to generatea stimulation signal adapted to stimulate an autonomic neural target.The analyzer is adapted to, in response to a PVC event signal from thePVC event detector, generate an autonomic balance indicator (ABI) as afunction of pre-PVC heart rate data and post-PVC heart rate data.

Various aspects of the present subject matter relate to a method.According to various embodiments of the method, an autonomic neuraltarget is stimulated, a PVC event is identified, and pre-PVC heart ratedata and post-PVC heart rate data are detected. An autonomic balanceindicator (ABI) is generated as a function of the pre-PVC heart ratedata and the post-PVC heart rate data in response to the PVC event.

This Summary is an overview of some of the teachings of the presentapplication and not intended to be an exclusive or exhaustive treatmentof the present subject matter. Further details about the present subjectmatter are found in the detailed description and appended claims. Otheraspects will be apparent to persons skilled in the art upon reading andunderstanding the following detailed description and viewing thedrawings that form a part thereof, each of which are not to be taken ina limiting sense. The scope of the present invention is defined by theappended claims and their equivalents.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a neural stimulator with autonomic balance feedback,according to various embodiments of the present subject matter.

FIGS. 2A and 2B illustrate an embodiment to control autonomic neuralstimulation and an embodiment to determine neural stimulation capture,respectively, according to various embodiments of the present subjectmatter.

FIGS. 2C-2E illustrate timing diagrams for embodiments of the presentsubject matter.

FIG. 2F illustrates a method for determining an autonomic balanceindicator for use in controlling an autonomic neural stimulator,according to various embodiments of the present subject matter.

FIG. 3 illustrates a timeline with a PVC event, pre-PVC heart rate data,and post-PVC heart rate data, according to various embodiments of thepresent subject matter.

FIG. 4 illustrates a timeline where ABIs are periodically determined atdiscrete times, according to various embodiments of the present subjectmatter.

FIG. 5 illustrates a timeline where ABIs are intermittently determinedat discrete times, according to various embodiments of the presentsubject matter.

FIG. 6 illustrates a logic circuit for use to trigger an analysis of anABI, according to various embodiments of the present subject matter.

FIG. 7 illustrates an analyzer, such as illustrated in FIG. 1, accordingto various embodiments of the present subject matter.

FIG. 8 illustrates an embodiment of a control system for an embodimentof an implantable medical device (MID) which monitors the autonomicnervous system (ANS) to control neural stimulation of a neural targetwithin the ANS.

FIG. 9A illustrates an embodiment of a method to adjust neuralstimulation based on sensed parameter(s), such as may be performed by animplantable medical device (IMD) or programmer, for example.

FIG. 9B illustrates an embodiment of a method to adjust neuralstimulation based on sensed parameter(s) reported to a physician for useby the physician to select a neural stimulation setting, for example.

FIG. 10 illustrates an implantable medical device (IMD) having a neuralstimulator (NS) component and cardiac rhythm management (CRM) component,according to various embodiments of the present subject matter.

FIG. 11 shows a system diagram of an embodiment of amicroprocessor-based implantable device.

FIGS. 12-15 generally illustrate examples of systems that include animplantable neural stimulator with autonomic balance feedback determinedusing a PVC, according to various embodiments.

DETAILED DESCRIPTION

The following detailed description of the present subject matter refersto the accompanying drawings which show, by way of illustration,specific aspects and embodiments in which the present subject matter maybe practiced. These embodiments are described in sufficient detail toenable those skilled in the art to practice the present subject matter.Other embodiments may be utilized and structural, logical, andelectrical changes may be made without departing from the scope of thepresent subject matter. References to “an”, “one”, or “various”embodiments in this disclosure are not necessarily to the sameembodiment, and such references contemplate more than one embodiment.The following detailed description is, therefore, not to be taken in alimiting sense, and the scope is defined only by the appended claims,along with the full scope of legal equivalents to which such claims areentitled.

Various aspects of the present subject matter monitor autonomic balancefor use in titrating a neural stimulation therapy. Various aspects ofthe present subject matter monitor autonomic balance for use indetermining whether neural stimulation is capturing the appropriateneural networks. A value for the autonomic balance is determined atdiscrete times corresponding to premature ventricular contractions(PVC). The autonomic balance value is based on the heart rate before thePVC and the heart rate after the PVC. The PVC can be detected,naturally-occurring PVC or an induced PVC. The autonomic balance valuescan be trended over a period of time to determine the efficacy of theneural therapy. Benefits include the ability to quickly determine, innear real time, a value for autonomic balance. The autonomic balancevalue can be found at discrete times with relatively small requirementsfor power and for data processing and storage.

Provided below is a brief discussion of the autonomic nervous system,and methods for assessing autonomic balance, including a briefcomparison of Heart Rate Turbulence (HRT) to Heart Rate Variability(HRV). Neural stimulation therapy examples, with and without myocardialstimulation therapy, are discussed. This disclosure concludes withexamples of implantable medical devices and methods, and examples ofimplantable medical device systems.

Autonomic Nervous System

The automatic nervous system (ANS) regulates “involuntary” organs, whilethe contraction of voluntary (skeletal) muscles is controlled by somaticmotor nerves. Examples of involuntary organs include respiratory anddigestive organs, and also include blood vessels and the heart. Often,the ANS functions in an involuntary, reflexive manner to regulateglands, to regulate muscles in the skin, eye, stomach, intestines andbladder, and to regulate cardiac muscle and the muscle around bloodvessels, for example.

The ANS includes, but is not limited to, the sympathetic nervous systemand the parasympathetic nervous system. The sympathetic nervous systemis affiliated with stress and the “fight or flight response” toemergencies. Among other effects, the “fight or flight response”increases blood pressure and heart rate to increase skeletal muscleblood flow, and decreases digestion to provide the energy for “fightingor fleeing.” The parasympathetic nervous system is affiliated withrelaxation and the “rest and digest response” which, among othereffects, decreases blood pressure and heart rate, and increasesdigestion to conserve energy. The ANS maintains normal internal functionand works with the somatic nervous system.

Stimulating the sympathetic and parasympathetic nervous systems can havea number of physiological effects. For example, stimulating variousportions of the sympathetic nervous system dilates the pupil, reducessaliva and mucus production, relaxes the bronchial muscle, reduces thesuccessive waves of involuntary contraction (peristalsis) of the stomachand the motility of the stomach, increases the conversion of glycogen toglucose by the liver, decreases urine secretion by the kidneys, andrelaxes the wall and closes the sphincter of the bladder. Stimulatingvarious portions of the parasympathetic nervous system (inhibiting thesympathetic nervous system) constricts the pupil, increases saliva andmucus production, contracts the bronchial muscle, increases secretionsand motility in the stomach and large intestine, and increases digestionin the small intention, increases urine secretion, and contracts walland relaxes the sphincter of the bladder. The functions associated withthe sympathetic and parasympathetic nervous systems are many and can becomplexly integrated with each other.

Autonomic Balance Assessment

Heart Rate Variability (HRV) is one technique that has been proposed toassess autonomic balance. The time interval between intrinsicventricular heart contractions changes in response to the body'smetabolic need for a change in heart rate and the amount of blood pumpedthrough the circulatory system. For example, during a period of exerciseor other activity, a person's intrinsic heart rate will generallyincrease over a time period of several or many heartbeats. However, evenon a beat to-beat basis, that is, from one heart beat to the next, andwithout exercise, the time interval between intrinsic heart contractionsvaries in a normal person. These beat-to-beat variations in intrinsicheart rate are the result of proper regulation by the autonomic nervoussystem of blood pressure and cardiac output; the absence of suchvariations indicates a possible deficiency in the regulation beingprovided by the autonomic nervous system. One method for analyzing HRVinvolves detecting intrinsic ventricular contractions, and recording thetime intervals between these contractions, referred to as the R-Rintervals, after filtering out any ectopic contractions (ventricularcontractions that are not the result of a normal sinus rhythm). Thissignal of R-R intervals is typically transformed into thefrequency-domain, such as by using fast Fourier transform (FFT)techniques, so that its spectral frequency components can be analyzedand divided into low and high frequency bands. For example, the lowfrequency (LF) band can correspond to a frequency (f) range 0.04Hz≦f<0.15 Hz, and the high frequency (HF) band can correspond to afrequency range 0.15 Hz≦f≦0.40 Hz. The HT band of the R-R intervalsignal is influenced only by the parasympathetic/vagal component of theautonomic nervous system. The LF band of the R-R interval signal isinfluenced by both the sympathetic and parasympathetic components of theautonomic nervous system. Consequently, the ratio LF/HF is regarded as agood indication of the autonomic balance between sympathetic andparasympathetic/vagal components of the autonomic nervous system. Anincrease in the LF/RF ratio indicates an increased predominance of thesympathetic component, and a decrease in the LF/HF ratio indicates anincreased predominance of the parasympathetic component. For aparticular heart rate, the LF/HF ratio is regarded as an indication ofpatient wellness, with a lower LF/HF ratio indicating a more positivestate of cardiovascular health. A spectral analysis of the frequencycomponents of the R-R interval signal can be performed using a FFT (orother parametric transformation, such as autoregression) technique fromthe time domain into the frequency domain. Such calculations requiresignificant amounts of data storage and processing capabilities.Additionally, such transformation calculations increase powerconsumption, and shorten the time during which the implantedbattery-powered device can be used before its replacement is required.

The present subject matter provides a neural stimulator that monitorsautonomic feedback. The neural stimulator provides a value for autonomicbalance at discrete times corresponding to premature ventricularcontractions (PVC) based on the heart rate for a predetermined number ofbeats before the PVC and the heart rate for a predetermined number ofbeats after the PVC.

Heart rate turbulence (HRT) is the physiological response of the sinusnode to a PVC, consisting of a short initial heart rate accelerationfollowed by a heart rate deceleration. HRT has been shown to be an indexof autonomic function, closely correlated to HRV. HRT is believed to bean autonomic baroreflex. The PVC causes a brief disturbance of thearterial blood pressure (low amplitude of the premature beat, highamplitude of the ensuing normal beat). This fleeting change isregistered immediately with an instantaneous response in the form of HRTif the autonomic system is healthy, but is either weakened or missing ifthe autonomic system is impaired.

By way of example and not limitation, it has been proposed to quantifyHRT using Turbulence Onset (TO) and Turbulence Slope (TS). TO refers tothe difference between the heart rate immediately before and after aPVC, and can be expressed as a percentage. For example, if two beats areevaluated before and after the PVC, TO can be expressed as:

${{TO}\mspace{14mu} \%} = {\frac{\left( {{RR}_{+ 1} + {RR}_{+ 2}} \right) - \left( {{RR}_{- 2} - {RR}_{- 1}} \right)}{\left( {{RR}_{- 2} - {RR}_{- 1}} \right)}*100.}$

RR⁻² RR⁻¹ are the first two normal intervals preceding the PVC and RR₊₁and RR₊₂ are the first two normal intervals following the PVC. Invarious embodiments, TO is determined for each individual PVC, and thenthe average value of all individual measurements is determined. However,TO does not have to be averaged over many measurements, hut can be basedon one PVC event. Positive TO values indicate deceleration of the sinusrhythm, and negative values indicate acceleration of the sinus rhythm.The number of R-R intervals analyzed before and after the PVC can beadjusted according to a desired application. TS, for example, can becalculated as the steepest slope of linear regression for each sequenceof five R-R intervals. In various embodiments, the TS calculations arebased on the averaged tachogram and expressed in milliseconds per R-Rinterval. However, TS can be determined without averaging. The number ofR-R intervals in a sequence used to determine a linear regression in theTS calculation also can be adjusted according to a desired application.

In its use of HRT, the present subject matter provides rules or criteriafor use to select PVCs and for use in selecting valid RR intervalsbefore and after the PVCs, A PVC event can be defined by an R-R intervalin some interval range that is shorter than a previous interval by sometime or percentage, or it can be defined by an R-R interval without anintervening P-wave (atrial event) if the atrial events are measured.Various embodiments select PVCs only if the contraction occurs at acertain range from the preceding contraction and if the contractionoccurs within a certain range from a subsequent contraction. Forexample, various embodiments limit the HRT calculations to PVCs with aminimum prematurity of 20% and a post-extrasystole interval which is atleast 20% longer than the normal interval. Additionally, pre-PVC R-R andpost-PVC RR intervals are considered to be valid if they satisfy thecondition that none of the beats are PVCs. One HRT process, for example,excludes R-R intervals that are less than a first time duration, thatare longer than a second time duration, that differ from a precedinginterval by more than a third time duration, or that differ from areference interval by a predetermined amount time duration orpercentage. In an embodiment of such an HRT process with specificvalues, RR intervals are excluded if they are less than 300 ms, are morethan 2000 ms, differ from a preceding interval by more than 200 ms, ordiffer by more than 20% from the mean of the last five sinus intervals.Various embodiments of the present subject matter provide programmableparameters, such as any of the parameters identified above, for use inselecting PVCs and for use in selecting valid R-R intervals before andafter the PVCs.

The neural stimulation device that incorporates this technique forassessing autonomic balance can be used to provide eitherparasympathetic stimulation or inhibition or sympathetic stimulation orinhibition. Various device embodiments include means for pacing aventricle, such as at least one ventricular pacing lead. To measureautonomic balance for closed-loop therapy titration, the deviceintermittently introduces or senses a PVC, and measures the resultingheart rate turbulence, as described above. In this way the therapyintensity can be increased or decreased according to the patient'sautonomic balance. Various embodiments introduce a PVC and monitorautonomic balance to verify that a neural stimulation therapy iscapturing the desired neural network. Various device embodiments performan auto-threshold detection, in which the device automatically adjustsneural stimulation parameters and/or neural stimulation target locationsuntil the desired autonomic balance reaction is observed. Otherembodiments report out a value for the autonomic balance for use inprogramming the neural stimulation.

Benefits of using HRT to monitor autonomic balance include the abilityto measure autonomic balance at a single moment in time. Additionally,unlike the measurement of HRV, HRT assessment can be performed inpatients with frequent atrial pacing. Further, HRT analysis provides fora simple, non-processor-intensive measurement of autonomic balance.Thus, data processing, data storage, and data flow are relatively small,resulting in a device with less cost and less power consumption. Also,HRT assessment is faster than HRV, requiring much less data. HRT allowsassessment over short recording periods similar in duration to typicalneural stimulation burst durations, such as on the order of tens ofseconds, for example.

Various implantable device embodiments provide autonomic stimulationtherapy. The device periodically or intermittently introduces PVC andmeasures HRT for closed-loop therapy titration and/or for auto-thresholddetermination. The present subject matter can be used in any patientpopulation which may benefit from autonomic neural stimulation therapy,including patients with heart failure, coronary artery disease,dysautonomia, and the like. However, the present subject matter is notsuitable for patients dependent on atrial pacing, because heart ratewill be controlled by the pacemaker rather than the cardiac autonomiccontrol system. In various embodiments, the present subject matter isimplemented in an implantable cardiac rhythm management (CRM) device,such as a pacemaker, an anti-tachycardia device such as a defibrillator,or cardioverter, CRT-pacing device, or CRT defibriliation/cardioversiondevice. According to various embodiments, the device detects thepresence of a PVC and calculates the resulting HRT. In some embodiments,the device artificially introduces a PVC and calculates the resultingHRT. In some embodiments, the device receives a message indicating a PVCevent has or will be occurring.

The following section discusses neural stimulation therapies, andprovides some information regarding pacing/cardioverting therapies, andCRT. These CRM functions can be used to detect a PVC or induce a PVC.There are other benefits of integrating a neural stimulator with a CRMdevice.

Therapy Examples

Embodiments of the present subject matter use autonomic balance as afeedback for neural stimulation, and embodiments of the present subjectmatter determine neural stimulation thresholds using an autonomicbalance indicator as a surrogate of capture.

NS: ABI to Titrate Neural Stimulation

According to an embodiment, an autonomic balance indicator (ABI)provides feedback to titrate neural stimulation therapy to achieve adesired autonomic balance. Various embodiments average or trend discreteautonomic balance measurements, and use the trended value as feedbackfor the neural stimulation control system. Thus, the present subjectmatter does not overcompensate with a neural stimulation adjustment inresponse to one or a few autonomic indicators. Embodiments of thepresent subject matter provide neural stimulation to an autonomic nerveto adjust the autonomic balance, and some embodiments stimulate anautonomic nerve (e.g. vagus) as part of various therapies such astherapies to treat obesity, epilepsy, breathing disorders, andhypertension.

According to a closed-loop system embodiment, the device is used toevaluate chronic autonomic balance condition concomitant with long-termneural stimulation therapy, and to adjust the neural stimulation levelto achieve a desired autonomic balance. According to some embodiments,the ABI may be determined during periods without neural stimulation orthe neural stimulation therapy may be interrupted to obtain an ABImeasure in order to measure a steady-state patient condition rather thana transient response to neural stimulation. Some embodiments determineABI at the beginning of neural stimulation, during neural stimulation,or at the end of neural stimulation.

According to various embodiments, the present subject matter providesneural stimulation to stimulate or inhibit the sympathetic system or tostimulate or inhibit the parasympathetic system. Some embodimentsincrease the amount of sympathetic nerve traffic to the myocardium totreat conditions in which an increase in heart rate or an increase inthe inotropic state of the heart is desirable. Examples of suchsituations include bradycardia and acute cardiac failure.

Some embodiments of the present subject matter pace the heart to treatarrhythmias by stimulating the autonomic nerves rather than stimulatingthe myocardium. The heart can be paced using the autonomic nervoussystem to provide chronotropic and inotropic control via selectivecardiac neural stimulation. The selective neural stimulation provide anatural stimulus for pacing.

Selective stimulation of epicardial autonomic ganglia can be used toselectively activate the parasympathetic nervous system. Embodiments ofthe present subject matter decrease left ventricular contractility viapostganglionic parasympathetic nervous system activity. The intrinsiccardiac ganglionated plexus integrate and process afferent and efferentautonomic nervous system activity. Some embodiments provide selectiveneural stimulation to provide specific cardiac pacing effects based onthe stimulated fat pad.

Embodiments of the present subject matter stimulate neural pathways tofine-tune autonomic balance to mitigate a number of cardiovasculardisorders. Ischemia, which may occur because of coronary artery disease,can cause increased sympathetic nervous system activity. This increasedsympathetic activity can result in increased exposure of the myocardiumto epinephrine and norepinephrine. These catecholamines activateintracellular pathways within the myocytes, which lead to myocardialdeath and fibrosis. Stimulation of the parasympathetic nerves inhibitsthe effect from the ischemia-induced increase in sympathetic activity.Some embodiments provide selective neural stimulation to increase vagaltone to reduce myocardial exposure to epinephrine, thus reducingmyocardial death and fibrosis. Some embodiments provide selective neuralstimulation to increase vagal tone to prevent post-MI patients fromfurther remodeling or predisposition to fatal arrhythmias. Someembodiments provide selective neural stimulation to provide autonomicbalance following ischemic insult to prevent the onset of lethalarrhythmias.

NS: ABI to Verify Neural Stimulation Capture

According to an embodiment, a neural stimulation threshold orauto-threshold system determines, using an ABI measurement, whether agiven neural stimulation evokes a response above some threshold. Thus, acertain ABI response is used to determine that a particular neuralstimulation is capturing the appropriate neural networks. For example,the threshold testing can apply demanded testing, such as testingtriggered by a physician command or an intermittent measurement based ontime. The testing could also be triggered by an event. A systemembodiment with demanded testing is able to stimulate PVCs on demand. Amethod embodiment includes triggering or requesting a threshold test,turning on the neural stimulation at a given level, recording thepre-PVC RR intervals, stimulating a PVC, recording the post-PVC RRintervals, and calculating the ABI during the neural stimulation usingthe pre-PVC and post-PVC RR intervals. The ABI measurement can bereported to a programmer, where a physician can manually take someaction or the programmer can automatically step the neural stimulationto the next level and trigger another test. The ABI can be used by theneural stimulator device to automatically step the neural stimulationand trigger another test. For example, the device can be programmed tolook for a “threshold” stimulation based on a specified ABI response andperform the auto-threshold test and adjust neural stimulation until the“threshold” is achieved, with some limits on the range of neuralstimulation levels. The device can store ABI values in memory or use theABI result to adjust the neural stimulation level.

Various embodiments verify stimulation capture at or near the time ofimplantation of a neural stimulator. A temporary pacing catheter can beimplanted, if an existing CRM lead is not already available, for use togenerate PVCs and whether the implanted stimulator is adequatelycapturing the neural stimulation. These induced PVCs can be used todetermine neural stimulation threshold and verify capture for theimplanted neural stimulator. Thus, such a system is useful to determinegood placement of a neural stimulator, such as placement of a neuralstimulator lead. Some embodiments use the system to select anappropriate electrical vector between or among available neuralstimulation electrodes. Some embodiments use ABI measurement(s) tootherwise focus the neural stimulation, such as focused ultrasoundstimulation, to provide selective neural stimulation.

According to various embodiments, the neural stimulation with anautonomic balance indicator is included in a system that has myocardialstimulation capabilities. The system can include at least one devicewith both CRM and neural stimulation functions in each device, and caninclude a CRM device and a neural stimulation device adapted tocommunicate with each other.

CRM: Pacing/Cardioverting (Defibrillating Anti-Tachycardia Pacing)

When functioning properly, the human heart maintains its own intrinsicrhythm, and is capable of pumping adequate blood throughout the body'scirculatory system. However, some people have irregular cardiac rhythms,referred to as cardiac arrhythmias. Such arrhythmias result indiminished blood circulation. One mode of treating cardiac arrhythmiasuses a CRM system. Such systems are often implanted in the patient anddeliver therapy to the heart.

CRM systems include, among other things, pacemakers. Pacemakers delivertimed sequences of tow energy electrical stimuli, called pace pulses, tothe heart intravascular leadwire or catheter (referred to as a “lead”)having one or more electrodes disposed in or about the heart can be usedto deliver the stimulation. Some embodiments use a “planet” IMDwirelessly connected to “satellite” electrodes to deliver thestimulation. Heart contractions are initiated in response to such pacepulses. By properly timing the delivery of pace pulses, the heart can beinduced to contract in proper rhythm, greatly improving its efficiencyas a pump. Pacemakers are often used to treat patients withbradyarrhythmias, that is, hearts that beat too slowly, or irregularly.

A variety of cardiac pacemakers are known and commercially available.Pacemakers are generally characterized by a number of different aspectsof their construction or use, such as which chambers of the heart theyare capable of sensing, the chambers to which they deliver pacingstimuli, and their responses, if any, to sensed intrinsic electricalcardiac activity. Some pacemakers deliver pacing stimuli at fixed,regular intervals without regard to naturally occurring cardiacactivity. Some pacemakers sense electrical cardiac activity in one ormore of the chambers of the heart, and inhibit or trigger delivery ofpacing stimuli to the heart based on the occurrence and recognition ofsensed intrinsic electrical events. One such pacemaker, for example,senses electrical cardiac activity in the ventricle of the patient'sheart, and delivers pacing stimuli to the ventricle only in the absenceof electrical signals indicative of natural ventricular contractions.Another type of pacemaker, on the other hand, senses electrical signalsin both the atrium and ventricle of the patient's heart, and deliversatrial pacing stimuli in the absence of signals indicative of naturalatrial contractions, and ventricular pacing stimuli in the absence ofsignals indicative of natural ventricular contractions. The delivery ofeach pacing stimulus by the second type of pacemaker is timed usingprior sensed or paced events.

Pacemakers are also known which respond to other types ofphysiologically-based signals, such as signals from sensors formeasuring the pressure inside the patient's ventricle or for measuringthe level of the patient's physical activity. In some rate-responsivepacemakers, the pacing rate is determined according to the output froman activity sensor. The pacing rate is variable between a predeterminedmaximum and minimum level, which may be selectable from among aplurality of programmable upper and tower rate limit settings. When theactivity sensor output indicates that the patient's activity level hasincreased, the pacing rate is increased from the programmed tower rateby an incremental amount which is determined as a function of the outputof the activity sensor.

CRM systems also include defibrillators that are capable of deliveringhigher energy electrical stimuli to the heart. Such defibrillators alsoinclude cardioverters, which synchronize the delivery of such stimuli toportions of sensed intrinsic heart activity signals. Defibrillators areoften used to treat patients with tachyarrhythmias, that is, hearts thatbeat too quickly. Such too-fast heart rhythms also cause diminishedblood circulation because the heart is not allowed sufficient time tofill with blood before contracting to expel the blood. Such pumping bythe heart is inefficient. A defibrillator is capable of delivering ahigh energy electrical stimulus that is sometimes referred to as adefibrillation countershock, also referred to simply as a “shock,” Thecountershock interrupts the tachyarrhythmia, allowing the heart toreestablish a normal rhythm for the efficient pumping of blood. Some CRMsystems also are pacemakers/defibrillators that combine the functions ofpacemakers and defibrillators, drug delivery devices, and any otherimplantable or external systems or devices for diagnosing or treatingcardiac arrhythmias. A cardioverter embodiment treats arrhythmias usinganti-tachycardia pacing,

CRM: Cardiac Resynchronization Therapy (CRT)

Following myocardial infarction (MI) or other cause of decreased cardiacoutput, a complex remodeling process of the ventricles occurs thatinvolves structural, biochemical, neurohormonal, and electrophysiologicfactors. Ventricular remodeling is triggered by a physiologicalcompensatory mechanism that acts to increase cardiac output due toso-called backward failure which increases the diastolic fillingpressure of the ventricles and thereby increases the so-called preload(i.e., the degree to which the ventricles are stretched by the volume ofblood in the ventricles at the end of diastole). An increase in preloadcauses an increase in stroke volume during systole, a phenomena known asthe Frank-Starling principle. When the ventricles are stretched due tothe increased preload over a period of time, however, the ventriclesbecome dilated. The enlargement of the ventricular volume causesincreased ventricular wall stress at a given systolic pressure. Alongwith the increased pressure-volume work done by the ventricle, this actsas a stimulus for hypertrophy of the ventricular myocardium. Thedisadvantage of dilatation is the extra workload imposed on normal,residual myocardium and the increase in wall tension (Laplace's Law)which represent the stimulus for hypertrophy. If hypertrophy is notadequate to match increased tension, a vicious cycle ensues which causesfurther and progressive dilatation.

As the heart begins to dilate, afferent baroreceptor and cardiopulmonaryreceptor signals are sent to the vasomotor central nervous systemcontrol center, which responds with hormonal secretion and sympatheticdischarge. The combination of hemodynamic, sympathetic nervous systemand hormonal alterations (such as presence or absence of angiotensinconverting enzyme (ACE) activity) accounts for the deleteriousalterations in cell structure involved in ventricular remodeling. Thesustained stresses causing hypertrophy induce apoptosis (i.e.,programmed cell death) of cardiac muscle cells and eventual wallthinning which causes further deterioration in cardiac function. Thus,although ventricular dilation and hypertrophy may at first becompensatory and increase cardiac output, the processes ultimatelyresult in both systolic and diastolic dysfunction has been shown thatthe extent of ventricular remodeling is positively correlated withincreased mortality in post-MI and heart failure patients.

The heart pumps more effectively when the chambers contract in acoordinated manner, a result normally provided by the specializedconduction pathways in both the atria and the ventricles that enable therapid conduction of excitation (i.e., depolarization) throughout themyocardium. These pathways conduct excitatory impulses from the sinθ-atrial node to the atrial myocardium, to the atrio-ventricular node,and thence to the ventricular myocardium to result in a coordinatedcontraction of both atria and both ventricles. This both synchronizesthe contractions of the muscle fibers of each chamber and synchronizesthe contraction of each atrium or ventricle with the contralateralatrium or ventricle. Without the synchronization afforded by thenormally functioning specialized conduction pathways, the heart'spumping efficiency is greatly diminished. Pathology of these conductionpathways and other inter-ventricular or inn-a-ventricular conductiondeficits can be a causative factor in heart failure, which refers to aclinical syndrome in which an abnormality of cardiac function causescardiac output to fall below a level adequate to meet the metabolicdemand of peripheral tissues. In order to treat these problems,implantable cardiac devices have been developed that provideappropriately timed electrical stimulation to one or more heart chambersin an attempt to improve the coordination of atrial and/or ventricularcontractions, termed CRT. Ventricular resynchronization is useful intreating heart failure because, although not directly inotropic,resynchronization can result in a more coordinated contraction of theventricles with improved pumping efficiency and increased cardiacoutput. Currently, a common form of CRT applies stimulation pulses toboth ventricles, either simultaneously or separated by a specifiedbiventricular offset interval, and after a specified atrio-ventriculardelay interval with respect to the detection of an intrinsic atrialcontraction or delivery of an atrial pace.

Clinical data has shown that CRT, achieved through synchronizedbiventricular pacing, results in a significant improvement in cardiacfunction. It has also been reported that CRT can be beneficial inpreventing and/or reversing the ventricular remodeling that often occursin post-MI and heart failure patients. Remodeling control therapy (RCT)can be provided by controlling ventricular activation with cardiacresynchronization pacing of the myocardium.

Neural stimulation can also be applied as part of CRT. Sympatheticinhibition, as well as parasympathetic activation, have been associatedwith reduced arrhythmia vulnerability following a myocardial infarction,presumably by increasing collateral perfusion of the acutely ischemicmyocardium and decreasing myocardial damage. Modulation of thesympathetic and parasympathetic nervous system with neural stimulationhas been shown to have positive clinical benefits, such as protectingthe myocardium from further remodeling and predisposition to fatalarrhythmias following a myocardial infarction. Thus, some embodimentsthat provide CRT includes anti-remodeling therapy (ART) by stimulatingthe baroreflex in order to inhibit sympathetic activity to provide agreater therapeutic benefit than either RCT or ART individually.Additional information regarding the use of neural stimulation foranti-remodeling therapy (ART) is provided in U.S. Pat. No. 7,260,431entitled “Combined Remodeling Control Therapy and Anti-RemodelingTherapy By Implantable Cardiac Device”, filed May 20, 2004, which isherein incorporated by reference in its entirety.

An implantable stimulating electrode is placed near autonomic nerves.Some embodiments use epicardial leads for epicardial stimulation of atarget neural stimulation site, some embodiments use intravascular leadsfor transvascular neural stimulation of a target neural stimulationsite, and some embodiments use intravascular leads adapted to puncture avessel for percutaneous stimulation of a target neural stimulation site,and some embodiments use a neural stimulation cuff electrode. The nervescan be stimulated using electrical stimulation pulses, or can bestimulated using other energy sources such as sound (e.g. ultrasound) orlight stimulation. An implantable pulse generator with programmablepulse generating features is attached to the electrode. Electricalactivation of the electrode(s) stimulates the target sympathetic orparasympathetic nerves anatomically located near the electrode(s) at astrength and frequency sufficient to elicit depolarization of theadjacent nerve(s).

Electrical neural stimulation may be applied near the myocardium. Someembodiments electrically stimulate autonomic nerves innervating themyocardium without eliciting depolarization and contraction of themyocardium directly because the threshold for neural depolarization(especially myelinated vagal nerve fibers of the parasympathetic nervoussystem) is much lower than that of myocardial tissue. Differingfrequencies of stimulation can be used so as to depolarize post (or prein case of vagal nerve stimulation) ganglionic nerve fibers. A stimulusresponse curve may be generated to determine the minimal thresholdrequired to elicit myocardial contraction, and still maintain neuraldepolarization of the site. Some embodiments time the neural stimulationwith the refractory period.

Some embodiments stimulate fat pads. Some embodiments stimulate anSVC-AO cardiac fat pad located proximate to a junction between asuperior vena cava and an aorta. Stimulation of the SVC-AO fat padspecifically reduces the contractility of the left ventricle, thusproviding a neural stimulation treatment for diseases such as heartfailure and/or post myocardial infarction remodeling. Some embodimentsstimulate a PV cardiac fat pad associated with an sinoatrial (SA) nodeand some embodiments stimulate an IVC-LA cardiac fat pad associated withan atrioventricular (AV) node. The PV cardiac fat pad is locatedproximate to a junction between a right atrium and right pulmonary vein,and the IVC-LA cardiac fat pad is located proximate to a junctionbetween an inferior vena cava and a left atrium. Stimulation of the PVcardiac fat pad reduces a sinus rate, and stimulation of the IVC-LA fatpad increases AV conduction, which affects timing between a contractionsin a right atrium and contractions in the right ventricle. Fat padstimulation activates parasympathetic efferents. Because fat pad gangliaform part of the efferent pathway, stimulation of cardiac fat padsdirectly effects cardiac tissue. For example, stimulating theparasympathetic efferents can selectively affect rate, and conduction.Stimulation of the parasympathetic also has post-ganglionic inhibitionof sympathetic outflow.

Satellite electrodes or leads can be used to deliver the selectiveneural stimulation to a cardiac neural stimulation site, and othernon-electrical neural stimulators can be used. Examples ofnon-electrical neural stimulators include stimulators that useultrasound and light energies, for example. Lead embodiments includeepicardial leads and intravascularly-fed leads. Various lead embodimentsare designed and positioned to provide multiple functions such assensing, pacing, anti-tachycardia therapy etc. in addition to neuralstimulation. Various embodiments use an epicardial, transvascular and/orpercutaneous approaches to elicit adjacent neural depolarization, thusavoiding direct neural contact with a stimulating electrode and reducingproblems associated with neural inflammation and injury associated withdirect contact electrodes.

Implantable Medical Device and Methods

FIG. 1 illustrates a neural stimulator with autonomic balance feedback,according to various embodiments of the present subject matter. Theillustrated neural stimulator 100 includes a controller 101 operablyconnected to neural stimulator circuitry 102 to generate a neuralstimulation signal 103 to stimulate neural target(s) a neural network104. Embodiments deliver the neural stimulation to the neural target(s)through at least one electrode positioned proximate to the neuraltarget. Other embodiments use other energy waves, such as ultrasound andlight energy waves, to stimulate the neural target. The illustratedneural stimulator 100 includes a heart rate detector 105. A heart ratedetector embodiment includes sensors to detect R-waves in a cardiogram,and circuitry to determine the R-R interval. Examples of sensors capableof being used to detect R-waves include leads in or around the heart,and a leadless ECG which includes electrodes on a housing of theimplantable device that sense volume-conducted cardiac electricalsignals. Various embodiments include a PVC sensor 106, variousembodiments include a PVC stimulator 107, and various embodimentsinclude both a PVC sensor and a PVC stimulator. A PVC sensor can sensean intrinsic or induced PVC. An example of a PVC stimulator is astimulator adapted to pace the right ventricle (RV). The illustratedneural stimulator 100 includes a PVC event detector 108, which receivesinputs from the PVC stimulator 107 and the PVC sensor 106 to determinewhen a PVC event occurs. The PVC event detector can receive a signalfrom the PVC stimulator indicating that a PVC stimulation was provided,and/or can sense and confirm that a PVC actually occurred in response tothe PVC stimulation.

The illustrated neural stimulator 100 includes an analyzer 109 thatreceives heart rate data 110 from the heart rate detector, and receivesa signal 111 from the PVC event detector that indicates when a PVC eventoccurs. The analyzer is adapted to process this information to determinean Autonomic Balance Indicator (ABI) 112. The ABI is processed as afunction of the heart rate before the PVC event and the heart rate afterthe PVC event. In various embodiments, the ABI values include the HRTvalues TO and TS. In various embodiments, these ABI values 112 arereceived by the controller 101 for use in titrating the neuralstimulation delivered by the neural stimulator circuitry 102. In variousembodiments, the ABI values are received by a controller to verifycapture; and the controller adjusted neural stimulationparameters/Attorney neural stimulation locations as part of anauto-capture process until the ABI values indicate the desired neuralstimulation result.

The illustrated neural stimulator 100 also includes sensor circuitry113, a clock 114, memory 115, and a transceiver 116. The sensorcircuitry 113 can include various sensors to sense neural stimulation,sensors to sense surrogates of neural stimulation, or sensors to furtheridentify the physiological state of the patient such as respiratory andactivity sensors. The clock 114 can be used by the controller 101 toenable the appropriate circuitry to enable an ABI analysis. Variousembodiments analyze ABI periodically at or about equal time intervals,and various embodiments analyze ABI intermittently at non-equal timeintervals. Some embodiments analyze ABI on demand as part of auser-controller programmer system and some embodiments are synchronizedwith neural stimulation “on” and/or neural stimulation “off” as part ofa neural stimulation threshold application. For example, someembodiments trigger the ABI analysis upon the detection of an event, andsome embodiments trigger the ABI at predetermined times within theneural stimulation therapy. In response to a trigger, the controllerenables ABI at 117, which enables the heart rate tracker to detect theheart rate (e.g. R-R, intervals). After a delay 118, the ABI enablesignal enables the PVC sensor 106 to begin sensing for a PVC. Thecontroller 101 can also generate a PVC stimulation signal at 119 afteran appropriate delay 120 after generating the ABI signal. The delay 118and the delay 120 do not need to be the same delay. For example, someembodiments will sense for a PVC for a predetermined amount of timebefore generating a PVC stimulation signal. The delays 118 and 120 areprovided to allow the heart rate detector to collect the pre-PVC heartrate data before a PVC can be detected and processed. The enable signalcan be terminated after the analyzer has the data required to generatethe ABI value. The memory 115 can store instructions operated on by thecontroller 101 to deliver the neural stimulation and analyze the ABI totitrate the neural stimulation. The memory can also store the ABI values121 and a time stamp 122 associated with each ABI value, A collection ofthese discrete measurements can be processed to determine theappropriate adjustments for the neural stimulation. Various embodimentsadjust the amplitude, frequency, burst frequency, morphology, pulsewidth or various combinations thereof of the stimulation signal. Theburst frequency can be adjusted by adjusting the burst duration and/orthe duty cycle of the signals. The controller also can send results tothe programmer for physician action, including reprogramming the neuralstimulator or accepting settings used in a threshold test. Thetransceiver 116 is used to communicate with another device, such as anexternal programmer. Programming instructions can be communicated to thedevice through the transceiver. Additionally, the transceiver is used totransmit device data and collected data from the neural stimulator tothe other device.

FIG. 1 illustrates separate modules to illustrate certain functionsperformed by the device. It is understood that certain of theillustrated modules can be combined. Thus, for example, the controller101 and analyzer 109 can function together as a process or module toperform TO and TS calculations, and to perform trending functions todetermine when the quantified autonomic balance indicates that theneural stimulation should be adjusted.

FIGS. 2A and 2B illustrate an embodiment to control autonomic neuralstimulation and an embodiment to determine neural stimulation capture,respectively, according to various embodiments of the present subjectmatter. With reference to the method illustrated in FIG. 2A, anautonomic balance indicator (ABI) is determined using pre and post-PVCheart rate data, and an autonomic neural stimulator is controlled basedon at least one ABI of at least one induced or intrinsic PVC event. Withreference to the method illustrated in FIG. 2B, an ABI is determinedusing pre and post-PVC heart rate data, and neural stimulation captureis determined based on at least one ABI for at least one induced orintrinsic PVC event. The ABI measurement(s) can be stored in memory ofthe implantable medical device, can be reported to an external devicesuch as a programmer, or can be used to vary the neural stimulationparameters and/or neural stimulation locations based on ABI(s) as partof an auto-capture routine.

FIGS. 2C-2E illustrate timing diagrams for embodiments of the presentsubject matter. FIG. 2C illustrates an embodiment in which ABI is beingdetermined at the time neural stimulation is applied; and FIG. 2Dillustrates an embodiment in which ABI is determined at the end ofneural stimulation. These embodiments permit the detection of ABIs thatcorrespond to time periods with and without neural stimulation. Suchembodiments may be useful to detect acute evoked responses to ABI. FIG.2E illustrates an embodiment in which a neural stimulation therapy isinterrupted to perform an ABI measurement. Such an embodiment may beuseful to detect a steady-state autonomic balance.

FIG. 2F illustrates a method for determining an autonomic balanceindicator for use in controlling an autonomic neural stimulator,according to various embodiments of the present subject matter. At 223,it is determined whether an enable signal has been received. In responseto an enable signal, pre-PVC heart rate data is collected at 224. Afterinitial pre-PVC heart rate data is collected, the process detects a PVCevent at 225. The pre-PVC heart rate data 224 continues be collecteduntil the PVC event 225 is detected. Various embodiments only detectintrinsic PVCs, various embodiments only induce or stimulate PVCs, andvarious embodiments perform a process to detect intrinsic PVCs, andstimulate PVCs. For example, in the illustrated embodiment, a process isperformed to detect PVCs at 226. If a PVC is not detected at 226 and ifa predetermined time has elapsed at 227, then a PVC is induced at 228.After an acceptable PVC occurs, post-PVC heart rate data is collected at229. At 230, the process determines an autonomic balance indicator (ABI)using the pre-PVC heart rate data and the post-PVC heart rate data. Asillustrated by line 231, the process can be repeated to collectadditional ABIs. At 232, the autonomic neural stimulator is controlledbased on the calculated ABI(s) for the PVC event(s).

FIG. 3 illustrates a timeline with a PVC event, pre-PVC heart rate data,and post-PVC heart rate data. As illustrated in the figure, an ABI valueis determined by pre-PVC heart rate data and post-PVC heart rate data.According to various embodiments, the illustrated pre-PVC heart ratedata includes a predetermined number of R-R intervals (e.g. 2 beats)that immediately precede the PVC event; and the illustrated post-PVCheart rate data includes a predetermined number of R-R intervals (e.g. 2beats) that immediately follow the PVC event. Also, ABI can be measuredperiodically or intermittently and recorded, without necessarilyresulting in a neural stimulation level adjustment.

FIG. 4 illustrates a timeline where ABIs are periodically determined atdiscrete times. The ABIs have been illustrated in FIG. 3. As illustratedin FIG. 4, the ABIs are determined at relatively constant timeintervals. For example, and not by way of limitation, an ABI can bedetermined at or about every hour, or every day or at any otherappropriate interval to titrate the autonomic neural therapy. It isnoted that, for some embodiments, it may take some time before anacceptable intrinsic PVC is detected for use in determining the ABI.

FIG. 5 illustrates a timeline where ABIs are intermittently determinedat discrete times. The time intervals between ABIs are not equal. Thesetime intervals can be preprogrammed based on a clock or can otherwise betriggered.

FIG. 6 illustrates a logic circuit for use to trigger an analysis of anABI, according to various embodiments of the present subject matter. TheABI enable analyzer can be formed as part of the controller 101 in FIG.1, for example. The illustrated ABI enable analyzer receives inputs froma clock and from event trigger(s). The event trigger(s) can be based onsensor data or changes in neural stimulation therapy or CRM therapy orprogrammer signal, for example. The ABI enable signal is generated basedon the time or detected event trigger(s).

FIG. 7 illustrates an analyzer, such as illustrated at 109 in the neuralstimulator device 100 of FIG. 1, according to various embodiments of thepresent subject matter. The illustrated analyzer 709 includes a functiongenerator 733, a first-in, first-out (FIFO) pre-PVC buffer 734, a FIFOpost-PVC buffer 735, an R-R detector input 736, and a PVC event detectorinput 737. When first enabled, successive R-R intervals are stored viaswitch 738 into the FIFO pre-PVC buffer 734. The buffer 734 can includedifferent numbers of registers 738 to store the R-R intervals. Forexample, one embodiment includes two registers adapted to store twoconsecutive R-R intervals, and one embodiment includes five registersadapted to store five consecutive R-R intervals. Once the buffer 734 isfull, the oldest R-R interval is removed from the buffer when the nextR-R interval is received. Thus, the buffer stores a sequence of thelatest R-R intervals such that, upon a PVC event, the buffer stores theintervals immediately preceding the PVC event. Additionally, an enablesignal 739 is generated after the pre-PVC buffer is full, whichindicates that the analyzer is ready to process a PVC event. Asillustrated by the AND logic gate 740, when the PVC event occurs and theenable signal is present, a signal 741 is generated to actuate theswitch 738 and store subsequent R-R intervals in the FIFO post-PVCbuffer 735. The buffer 735 can include different numbers of registers742 to store the R-R intervals. For example, one embodiment includes tworegisters adapted to store two consecutive R-R intervals, and oneembodiment includes five registers adapted to store five consecutive R-Rintervals. When the buffer is full, the function generator 733 respondsto an enable signal 743 to use the pre-PVC heart rate data stored in thepre-PVC buffer and the post-PVC heart rate data stored in the post-PVCbuffer to generate an ABI value. The switch can be reset to begin toreceive R-R intervals in the pre-PVC buffer in response to the next ABIenable signal.

FIG. 8 illustrates an embodiment of a control system for an embodimentof an implantable medical device (MD) which monitors the autonomicnervous system (ANS) to control neural stimulation of a neural targetwithin the ANS. The includes controller circuitry 845, a neuralstimulator 846 which can also be referred to as a pulse generator, andan HRT analyzer 847. The illustrated controller 845 includes a feedbackcomparator 844 which can be referred to as an error detector, and aneural stimulation controller 849.

The illustrated controller circuitry 845 also includes a memory orregister 850 where values for various parameters can be programmed by anexternal programmer using a transceiver. Various embodiments allow oneor more of the following parameter types to be programmed: HRTparameters 851, stimulation parameters 852, and dynamic input selection853A. The illustrated HRT parameters include programmed parameters 854Afor low and high thresholds for R-R intervals and other parameters usedto determine whether to accept a PVC as a PVC event, and a desiredtarget parameter (or desired range of parameters) 855A. The illustratedstimulation parameters 852 include stimulation parameter(s) to beadjusted 856A in response to a feedback control signal, and availablegain increment(s) 857A for the adjustable stimulation parameter(s).These programmable parameters illustrated in memory 850 provide controlinputs to various modules of the device. In the illustrated embodiment,the programmable HRT parameter(s) 854A provide a control signal 854B tothe HRT analyzer 847 for use in adjusting the way in which the HRTvalues are calculated. The programmable adjustable stimulationparameters 856A provide a control signal 856B to the neural stimulator846 that indicates the parameters of the stimulation waveform to beadjusted. The programmable target 855A provides a control signal 855B tothe feedback comparator 844, the programmable gain increment 857Aprovides a control signal 857B to the neural stimulator controller 849that indicates an appropriate gain (positive and negative to incrementor decrement the stimulation intensity resulting from the stimulationvalues for the neural stimulation parameter(s). The programmable dynamicinput selection 853A provides a control signal 853B to the neuralstimulation controller to dynamically adjust the target range to accountfor other factors such as activity or time.

The HRT analyzes the heart rate, reflective of the health of theautonomic neural network, at time generally corresponding to the PVCevents. The illustrated HRT analyzer 847 responds to a PVC event byprocessing pre-PVC heart rate data and post-PVC heart rate data todetermine HRT data, which are output as the processed HRT signal. Aclock or timer can be used to determine when to perform HRT analysis.The feedback comparator 844 compares the HRT values (e.g. TO/TS) to thetarget parameter or target parameter range 855B for the sensedparameter(s). A result of the comparison is provided from the comparator844 to the neural stimulation controller 849 via a feedback resultsignal. The controller 849 receives the feedback result signal, anddelivers a stimulation control signal to the neural stimulator 846 basedon the feedback result signal. The neural stimulator 846 receives thestimulation control signal and controls the neural stimulation to adjustthe intensity of stimulation if appropriate to converge to the desiredHRT data as reflected by the comparison of processed HRT signal to thetarget 85513. According to various embodiments, the stimulator circuitry846 includes modules to set or adjust any one or any combination of twoor more of the following pulse features: the amplitude of thestimulation pulse, the frequency of the stimulation pulse, the burstfrequency of the pulse, the wave morphology of the pulse, and the pulsewidth. The illustrated burst frequency feature includes burst durationand duty cycle, which can be adjusted as part of a burst frequency pulsefeature or can be adjusted separately without reference to a steadyburst frequency.

In addition to the feedback result control input signal, someembodiments of the neural stimulation controller 849 also receive a gaincontrol input signal 857B used to provide the desired stimulationcontrol signal to the neural stimulator 846. It is noted that theintensity of the neural stimulation signal can be complexly related tothe parameters of the stimulation signal. Generally, an increasedamplitude of the signal increases neural stimulation. Additionally,there is a frequency window which corresponds to the highest neuralstimulation intensity, and frequencies that are either higher or lowerthan the frequency window provide less neural stimulation. Also,stimulated neural sites can quickly adapt to steady stimulation. Thus,adjustments in stimulation intensity can correspond to a variety ofadjustments to one or more of the amplitude of the stimulation pulse,the frequency of the stimulation pulse, the burst frequency of thepulse, the burst duration of the pulse, the duty cycle of thestimulation, the wave morphology of the pulse, and the pulse width. Thegain control adjusts the stimulation parameter(s) to achieve a desiredincrement or decrement in neural stimulation intensity. According tosome embodiments, the parameter adjustments are predetermined to providethe stimulation intensity adjustments. Some embodiments use an iterativeprotocol to determine the effects that parameter change(s) have onintensity. For example, according to some embodiments, the gain controlsignal 857B controls an algorithm used to methodically adjuststimulation parameter(s) that are available for adjustment, compare theresult to determine if the neural stimulation results in a result closerto the target or further from the target, and then adjust thestimulation parameter(s) again to achieve the desired increment ordecrement in the neural response. The same or different parameters canbe adjusted to achieve the desired response.

In addition to the feedback result control input signal, someembodiments of the neural stimulation controller 849 also receive adynamic control input signal used to provide the desired stimulationcontrol signal. The illustrated dynamic input 860 includes a clock 861and physiological sensor circuitry 862. The illustrated physiologicalsensor circuitry includes a heart rate sensor, an activity sensor, apressure sensor, and impedance sensor. Other physiological sensors canbe used. The dynamic input 863 enables the dynamic adjustment of theeffective operating target or target range based on a clock (e.g. acircadian rhythm) and/or based on physiological parameters. Thus, forexample, the dynamic input allows the target for the HRT values to bedifferent for someone exercising in the afternoon than sleeping in themiddle of the night, or can otherwise adjust the algorithms used tocalculate the HRT values. The dynamic input can be used in otherapplications. The selection of the dynamic input as well as theresulting control algorithms that use the dynamic input control signalcan be programmable. The illustrated controller circuitry 845 alsoincludes a PVC stimulator 807, such as illustrated at 107 in FIG. 1.

FIG. 9A illustrates an embodiment of a method to adjust neuralstimulation based on sensed parameter(s), such as may be performed by animplantable medical device (IMD) or programmer, for example. At 964, adetermination is made as to whether the sensed parameter(s) are withinthe target range. The sensed parameter(s) include HRT values (e.g. TO,TS). If the parameter(s) are determined to be within a target range, thestimulation settings are maintained 965 and the process returns to 964.If the parameter(s) are determined to be outside of a target range, theprocess proceeds to 966 to change the neural stimulation by at least onegain increment or decrement, depending on the arrangement, to move thesensed parameter(s) toward the target. Various embodiments provide otherranges above and/or below the target range; various embodiments providea target-sub-range within the target range, and various embodimentsfurther provide a number of other sub-ranges above and/or below thetarget sub-range; various embodiments provide a target sub-sub-rangewithin a target sub-range, and various embodiments further provide othersub-sub-ranges above and/or below the target sub-sub-range. Variousstimulation adjustment protocols (e.g. gain) can be used depending onthe range, sub-range and sub-sub-range. Thus, for example, largeadjustments can be made by adjusting one parameter (e.g. frequency) ofthe stimulation signal, and smaller adjustments can be made by adjustinganother parameter (e.g. amplitude) of a stimulation signal. Such amethod can use ABI(s) to titrate chronic neural stimulation or perform aneural stimulation auto-capture threshold test.

FIG. 9B illustrates an embodiment of a method to adjust neuralstimulation based on sensed parameter(s) reported to a physician for useby the physician to select a neural stimulation setting, for example.The method is similar to FIG. 9A, except that the ABI(s) arecommunicated to the physician, and the physician analyzes the data todetermine whether and how to change the stimulation.

FIG. 10 illustrates an implantable medical device (IMD) having a neuralstimulator (NS) component and cardiac rhythm management (CRM) component,according to various embodiments of the present subject matter. Theillustrated device 1067 includes a controller 1068 and a memory 1069.According to various embodiments, the controller 1068 includes hardware,software, or a combination of hardware and software to perform theneural stimulation and CRM functions. Examples of CRM functions include,for example, pacing, defibrillating, and cardiac resynchronizationtherapy (CRT) functions. For example, the programmed therapyapplications discussed in this disclosure are capable of being stored ascomputer-readable instructions embodied in memory and executed by aprocessor. According to various embodiments, the controller includes aprocessor to execute instructions embedded in memory to perform theneural stimulation and CRM functions. The illustrated device 1067further includes a transceiver 1070 and associated circuitry for use tocommunicate with a programmer or another external or internal device.Various embodiments include a telemetry coil.

The CRM therapy section 1071 includes components, under the control ofthe controller, to stimulate a heart and/or sense cardiac signals usingone or more electrodes. The CRM therapy section includes a pulsegenerator 1072 for use to provide an electrical signal through anelectrode to stimulate a heart, and further includes sense circuitry1073 to detect and process sensed cardiac signals or otherwise detectheart rate parameters according to the present subject matter. Thus, forexample, sense circuitry 1073 can be used to detect a PVC and to detectR—R intervals, and the pulse generator 1072 can be used to induce a PVC.An interface 1074 is generally illustrated for use to communicatebetween the controller 1068 and the pulse generator 1072 and sensecircuitry 1073. Three electrodes are illustrated as an example for useto provide CRM therapy. However, the present subject matter is notlimited to a particular number of electrode sites. One or moreelectrodes can be positioned on a lead, and one or more leads can beused. Each electrode may include its own pulse generator and sensecircuitry. However, the present subject matter is not so limited. Thepulse generating and sensing functions can be multiplexed to functionwith multiple electrodes.

The NS therapy section 1075 includes components, under the control ofthe controller, to stimulate neural target(s) and sense ANS parametersassociated with nerve activity, and in some embodiments sense surrogatesof ANS parameters such as blood pressure and respiration. Examples of NStherapy include, but are not limited to, therapies to treathypertension, epilepsy, obesity and breathing disorders. Threeinterfaces 1076 are illustrated for use to provide ANS therapy. However,the present subject matter is not limited to a particular numberinterfaces, or to any particular stimulating or sensing functions. Pulsegenerators 1077 are used to provide electrical pulses to an electrodefor use to stimulate a neural target. According to various embodiments,the pulse generator includes circuitry to set, and in some embodimentschange, the amplitude of the stimulation pulse, the frequency of thestimulation pulse, the burst frequency of the pulse, and/or themorphology of the pulse such as a square wave, triangle wave, sinusoidalwave, and waves with desired harmonic components to mimic white noise orother signals. Sense circuits 1078 are used to detect and processsignals from a sensor, such as a sensor of nerve activity, pulsatileparameters, blood pressure, respiration, and the like. The interfaces1076 are generally illustrated for use to communicate between thecontroller 1068 and the pulse generator 1077 and sense circuitry 1078.Each interface, for example, may be used to control a separate lead.Various embodiments of the NS therapy section only include a pulsegenerator to stimulate a neural target.

FIG. 11 shows a system diagram of an embodiment of amicroprocessor-based implantable device. The device is equipped withmultiple sensing and pacing channels which may be physically configuredto sense and/or pace multiple sites in the atria or the ventricles, andto provide neural stimulation. The illustrated device can be configuredfor myocardial stimulation (pacing, defibrillation, CRT/RCT) and neuralstimulation (therapy of sleep disordered breathing, CRM. CRT/ART). Themultiple sensing/pacing channels may be configured, for example, withone atrial and two ventricular sensing/pacing channels for deliveringbiventricular resynchronization therapy, with the atrial sensing/pacingchannel used to deliver the biventricular resynchronization therapy inan atrial tracking mode as well as to pace the atria if required. Theventricle pacing channel(s) can be used to induce a PVC and theventricle sensing channel(s) can be used to sense a PVC and sense R-Rintervals. The controller 1179 of the device is a microprocessor whichcommunicates with memory 1180 via a bidirectional data bus. Thecontroller could be implemented by other types of logic circuitry (e.g.,discrete components or programmable logic arrays) using a state machinetype of design. As used herein, the term “circuitry” should be taken torefer to either discrete logic circuitry or to the programming of amicroprocessor.

Shown in FIG. 11, by way of example, are three sensing and pacingchannels, such as can be used to provide myocardial stimulation/pacing,designated “A” through “C” comprising bipolar leads with ring, orproximal, electrodes 1181A-C and distal, or tip, electrodes 1182A-C,sensing amplifiers 1183A-C, pulse generators 1184A-C, and channelinterfaces 1185A-C. Each channel thus includes a pacing channel made upof the pulse generator connected to the electrode and a sensing channelmade up of the sense amplifier connected to the electrode. The channelinterfaces 1185A-C communicate bidirectionally with the microprocessor1179, and each interface may include analog-to-digital converters fordigitizing sensing signal inputs from the sensing amplifiers andregisters that can be written to by the microprocessor in order tooutput pacing pulses, change the pacing pulse amplitude, and adjust thegain and threshold values for the sensing amplifiers. The sensingcircuitry of the pacemaker detects a chamber sense, either an atrialsense or ventricular sense, when an electrogram signal (i.e., a voltagesensed by an electrode representing cardiac electrical activity)generated by a particular channel exceeds a specified detectionthreshold. Pacing algorithms used in particular pacing modes employ suchsenses to trigger or inhibit pacing, and the intrinsic atrial and/orventricular rates can be detected by measuring the time intervalsbetween atrial and ventricular senses, respectively.

The electrodes of each bipolar lead are connected via conductors withinthe lead to a switching network 1186 controlled by the microprocessor.The switching network is used to switch the electrodes to the input of asense amplifier in order to detect intrinsic cardiac activity and to theoutput of a pulse generator in order to deliver a pacing puke. Theswitching network also enables the device to sense or pace either in abipolar mode using both the ring, or proximal, and tip, or distal,electrodes of a lead or in a unipolar mode using only one of theelectrodes of the lead with the device housing or can 1187 serving as aground electrode.

Also shown in FIG. 11 by way of example, are nerve stimulation channelsdesignated “D” and “E.” Neural stimulation channels are incorporatedinto the device. These channels can be used to deliver neuralstimulation, such as for ART as part of CRT. The illustrated channelsinclude leads with electrodes 1188D and 1189D and electrodes 1188E and1189E, a puke generator 1190D and 1190E, and a channel interface 1191Dand 1191E. The illustrated bipolar arrangement is intended as anon-exclusive example. Other neural stimulation electrode arrangementsare within the scope of the present subject matter. Other embodimentsmay use unipolar leads in which case the neural stimulation pulses arereferenced to the can or another electrode. The pulse generator for eachchannel outputs a train of neural stimulation pulses which my be variedby the controller as to amplitude, frequency, duty-cycle, pulseduration, and wave morphology, for example.

A shock pulse generator 1192 is also interfaced to the controller fordelivering a defibrillation shock via a pair of shock electrodes 1193 tothe atria or ventricles upon detection of a shockable tachyarrhythmia.

The illustrated controller includes a module for controlling neuralstimulation (NS) therapy and module for controlling myocardial therapy.As illustrated, the NS therapy module includes a module for performingan autonomic neural stimulation. Also as illustrated, the myocardialtherapy module includes a module for controlling pacing therapies, amodule for controlling defibrillation therapies, and a module forstimulating a PVC. The illustrated controller is also adapted to controlCRT by controlling RCT (a myocardial stimulation therapy), and in someembodiments by controlling ART (a neural stimulation therapy).

The controller controls the overall operation of the device inaccordance with programmed instructions stored in memory, includingcontrolling the delivery of paces via the pacing channels, interpretingsense signals received from the sensing channels, and implementingtimers for defining escape intervals and sensory refractory periods. Thecontroller is capable of operating the device in a number of programmedpacing modes which define how pulses are output in response to sensedevents and expiration of time intervals. Most pacemakers for treatingbradycardia are programmed to operate synchronously in a so-calleddemand mode where sensed cardiac events occurring within a definedinterval either trigger or inhibit a pacing pulse. Inhibited demandpacing modes utilize escape intervals to control pacing in accordancewith sensed intrinsic activity such that a pacing pulse is delivered toa heart chamber during a cardiac cycle only after expiration of adefined escape interval during which no intrinsic beat by the chamber isdetected. Escape intervals for ventricular pacing can be restarted byventricular or atrial events, the latter allowing the pacing to trackintrinsic atrial beats, CRT is most conveniently delivered inconjunction with a bradycardia pacing mode where, for example, multipleexcitatory stimulation pulses are delivered to multiple sites during acardiac cycle in order to both pace the heart in accordance with abradycardia mode and provide pre-excitation of selected sites. Anexertion level sensor 1194 (e.g., an accelerometer, a minute ventilationsensor, or other sensor that measures a parameter related to metabolicdemand) enables the controller to adapt the pacing rate in accordancewith changes in the patient's physical activity and can enable thecontroller to modulate the delivery of neural stimulation and/or cardiacpacing. A telemetry interface 1195 is also provided which enables thecontroller to communicate with an external programmer or remote monitor.

Systems with IMD

FIGS. 12-15 generally illustrate examples of systems that include animplantable neural stimulator with autonomic balance feedback determinedusing a PVC, according to various embodiments, FIG. 12 illustrates asystem embodiment with an IMD 1201 and programmer 1202 capable ofwirelessly communicating with the IMD 1201. Thus, the programmer can beused to adjust the programmed therapy provided by the and the IMD canreport device data (such as battery and lead resistance) and therapydata (such as sense and stimulation data) to the programmer using radiotelemetry, for example. The illustrated IMD can include both neuralstimulation capabilities with autonomic balance feedback and CPAcapabilities, as discussed within this disclosure. The systemillustrated in FIG. 12 can also be used for neural stimulation thresholdmeasurement. FIG. 13 illustrates a system embodiment with an implantableneural stimulator 1303, an implantable CRM device 1304, and a programmer1302 capable of wirelessly communicating with at least one of the neuralstimulator 1303 and CRM device 1304. Thus, the programmer can be used toadjust the programmed therapy provided by the devices, and the devicescan report device data (such as battery and lead resistance) and therapydata (such as sense and stimulation data) to the programmer using radiotelemetry, for example. The devices 1303 and 1304 are adapted tocommunicate with each other to integrate the therapies. For example, theCRM device 1304 can be used to detect and/or induce PVCs, and detectpre-PVC heart rate data and post-PVC heart rate data for use indetermining ABIs to appropriately titrate the neural stimulation therapyaccording to an assessed autonomic balance. HRT calculations can beperformed in either device 1303 or 1304. An example of the systemillustrated in FIG. 13 includes a programmer serving as a communicationlink between the neural stimulator and CRM devices. For example, theprogrammer can set up some neural stimulation parameters, trigger aneural stimulation sequence, instruct the CRM to stimulate a PVC, andmeasure HRT during the neural stimulation. The HRT data would bereturned to the programmer, which then alters the neural stimulationparameters and repeats or programs selected neural stimulationparameters and finishes.

FIG. 14 illustrates a system embodiment in which an IMD 1405 is placedsubcutaneously or submuscularly in a patient's chest with lead(s) 1406positioned to stimulate a vagus nerve. According to various embodiments,neural stimulation lead(s) 1406 are subcutaneously tunneled to a neuraltarget, and can have a nerve cuff electrode to stimulate the neuraltarget. Some vagus nerve stimulation lead embodiments areintravascularly fed into a vessel proximate to the neural target, anduse electrode(s) within the vessel to transvascularly stimulate theneural target. For example, some embodiments stimulate the vagus usingelectrode(s) positioned within the internal jugular vein. Otherembodiments deliver neural stimulation to the neural target from withinthe trachea, the laryngeal branches of the internal jugular vein, andthe subclavian vein. The neural targets can be stimulated using otherenergy waveforms, such as ultrasound and light energy waveforms. Otherneural targets can be stimulated, such as cardiac nerves and cardiac fatpads. The illustrated system includes leadless ECG electrodes on thehousing of the device. These ECG electrodes 1408 are capable of beingused to detect a PVC. Various embodiments include cardiac leads, notillustrated, capable of inducing a PVC. Such cardiac leads can be usedto sense PVCs instead of wireless ECGs.

FIG. 15 illustrates a system embodiment that includes an implantablemedical device (IMD) 1505 with satellite electrode(s) 1507 positioned tostimulate at least one neural target. The satellite electrode(s) areconnected to the IMD, which functions as the planet for the satellites,via a wireless link. Stimulation and communication can be performedthrough the wireless link. Examples of wireless links include RF linksand ultrasound links. Examples of satellite electrodes includesubcutaneous electrodes, nerve cuff electrodes and intravascularelectrodes. Various embodiments include satellite neural stimulationtransducers used to generate neural stimulation waveforms such asultrasound and light waveforms. The illustrated system includes leadlessECG electrodes on the housing of the device. These ECG electrodes 1508are capable of being used to detect a PVC. Various embodiments includecardiac leads, not illustrated, capable of inducing a PVC. Such cardiacleads can be used to sense PVCs instead of wireless ECGs.

One of ordinary skill in the art will understand that, the modules andother circuitry shown and described herein can be implemented usingsoftware, hardware, and combinations of software and hardware. As such,the term module is intended to encompass software implementations,hardware implementations, and software and hardware implementations.

The methods illustrated in this disclosure are not intended to beexclusive of other methods within the scope of the present subjectmatter. Those of ordinary skill in the art will understand, upon readingand comprehending this disclosure, other methods within the scope of thepresent subject matter. The above-identified embodiments, and portionsof the illustrated embodiments, are not necessarily mutually exclusive.These embodiments, or portions thereof, can be combined. In variousembodiments, the methods provided above are implemented as a computerdata signal embodied in a carrier wave or propagated signal, thatrepresents a sequence of instructions which, when executed by aprocessor cause the processor to perform the respective method. Invarious embodiments, methods provided above are implemented as a set ofinstructions contained on a computer-accessible medium capable ofdirecting a processor to perform the respective method. In variousembodiments, the medium is a magnetic medium, an electronic medium, oran optical medium.

Although specific embodiments have been illustrated and describedherein, it will be appreciated by those of ordinary skill in the artthat any arrangement which is calculated to achieve the same purpose maybe substituted for the specific embodiment shown. This application isintended to cover adaptations or variations of the present subjectmatter. It is to be understood that the above description is intended tobe illustrative, and not restrictive. Combinations of the aboveembodiments as well as combinations of portions of the above embodimentsin other embodiments will be apparent to those of skill in the art uponreviewing the above description. The scope of the present subject mattershould be determined with reference to the appended claims, along withthe full scope of equivalents to which such claims are entitled.

1. A method, comprising: using an implantable device to deliver neuralstimulation to a neural stimulation site, detect heart rate, perform aplurality of heart rate turbulence (HRT) at a plurality of discretetimes using the detected heart to identify a plurality of HRTmeasurement values record the plurality of HRT measurement values in amemory of the implantable device, and record in the memory a timecorresponding to each of the measurement values; and verifying neuralstimulation capture using the recorded HRT measurement values and times.2. The method of claim 1, wherein the neural stimulation site can adaptto neural stimulation, and wherein verifying neural stimulation captureincludes identifying changes in a threshold for neural stimulationcapture attributed to neural stimulation adaptation.
 3. The method ofclaim 1, further comprising reporting data useful for verifying neuralstimulation capture from the implantable device to an external device.4. The method of claim 3, wherein verifying neural stimulation captureincludes using the external device to verify neural stimulation capture.5. The method of claim 3, further comprising monitoring heart failureusing the data reported to the external device.
 6. The method of claim3, further comprising monitoring therapy effectiveness using the datareported to the external device.
 7. The method of claim 1, wherein usingthe implantable device to deliver neural stimulation includesintermittently delivering neural stimulation using the implantabledevice to control neural stimulation ON timing and stimulation OFFtiming.
 8. The method of claim 1, further comprising trending the HRTmeasurement values.
 9. The method of claim 1, further comprisingaveraging the HRT measurement values.
 10. The method of claim 1, furthercomprising using the implantable device to record detected heart rate ina first-in first-out (FIFO) butler, to sense a premature ventricularcontraction (PVC), and to respond to the sensed PVC to measure HRT usingthe detected heart rate data in the FIFO buffer.
 11. The method of claim1, further comprising using the implantable device to record detectedheart rate in a first-in first-out (FIFO) buffer, to deliver aventricular pace to induce a premature ventricular contraction (PVC),and to measure HRT when the PVC is induced using the detected heart ratedata in the FIFO buffer.
 12. The method of claim 1, further comprisingusing a preprogrammed schedule in the implantable device to controltiming of the plurality of HRT measurements at the plurality of discretetimes.
 13. The method of claim 1, further comprising triggering HRTmeasurements based on sensor data, or therapy changes, or an externalsignal.
 14. A neural stimulation system for stimulating a neuralstimulation site that can adapt to neural stimulation, the systemcomprising: a neural stimulator configured to stimulate the neuralstimulation site; a memory; a heart rate detector configured to detectheart rate; an analyzer operably connected to the heart rate detector,wherein the analyzer is configured to measure heart rate turbulence(HRT); a clock; and a controller operably connected to the neuralstimulator, the analyzer and the clock, wherein the controller isconfigured to: control the neural stimulator to control the stimulationof the neural stimulation site; and perform a process useful forverifying neural stimulation capture of the neural stimulation site thatcan adapt to neural stimulation, wherein in performing the process, thecontroller is configured to: control the analyzer to perform a pluralityof HRT measurements at a plurality of discrete times during thestimulation; record measurement values for the plurality of HRTmeasurements in the memory; and record a time, corresponding to each ofthe measurement values, in the memory.
 15. The system of claim 14,wherein the controller is configured to control neural stimulation ONtiming and neural stimulation OFF timing.
 16. The system of claim 14,wherein the controller is configured to perform a calculation using theplurality of HRT measurements.
 17. The system of claim 14, furthercomprising a logic circuit configured to trigger an HRT measurement inresponse to an event trigger, wherein the device is configured toprovide the event trigger based on sensor data, based on therapychanges, or based on an external signal.
 18. An implantable medicaldevice for stimulating a neural stimulation site that can adapt toneural stimulation, the device comprising: a neural stimulatorconfigured to stimulate the neural stimulation site; a memory; a heartrate detector configured to detect heart rate; an analyzer operablyconnected to the heart rate detector, wherein the analyzer is configuredto measure heart rate turbulence (HRT); a transceiver; a clock; and acontroller operably connected to the neural stimulator, the analyzer,the transceiver and the clock, wherein the controller is configured tocontrol neural stimulation ON timing and neural stimulation OFF timing,wherein the controller is configured to: control the neural stimulatorto control the stimulation of the neural stimulation site; and perform aprocess useful for verifying neural stimulation capture, wherein inperforming the process, the controller is configured to: control theanalyzer to perform a plurality of HRT measurements at a plurality ofdiscrete times during the stimulation; record measurement values for theplurality of HRT measurements in the memory; and record a time,corresponding to each of the measurement values, in the memory; and usethe transceiver to transmit from the implantable medical device to anexternal device data useful for verifying neural stimulation capture.19. The device of claim 18, wherein the controller is configured tocontrol the analyzer to measure HRT at relatively constant timeintervals.
 20. The device of claim 18, wherein the controller isconfigured to control the analyzer to intermittently measure HRT atnon-equal time intervals.
 21. The device of claim 18, wherein thecontroller is configured to control the analyzer to measure HRT atpre-programmed time intervals.
 22. The device of claim 18, wherein theanalyzer is configured to use detected heart rate before a prematureventricular contraction (PVC) and detected heart rate after the PVC tomeasure HRT, record detected heart rate data in a first-in first-out(FIFO) buffer, and sense the PVC, wherein the analyzer is configured usethe detected heart rate data in the FIFO buffer as the detected heartrate before the PVC.
 23. The device of claim 18, wherein the analyzer isconfigured to use detected heart rate before a premature ventricularcontraction (PVC) and detected heart rate after the PVC to measure HRT,further comprising a PVC stimulator configured to deliver a ventricularpace to induce the PVC, wherein the analyzer is configured to recorddetected heart rate data in a first-in first-out (FIFO) buffer, andwherein the controller is configured to control the PVC stimulator toinduce the PVC.
 24. The device of claim 18, wherein the controller isconfigured to use the recorded measurement values to adjust thestimulation of the neural stimulation site.
 25. A implantable medicaldevice, comprising: a memory; a heart rate detector configured to detectheart rate; an analyzer operably connected to the heart rate detector,wherein the analyzer is configured to measure heart rate turbulence(HRT); a clock configured to monitor time; and a controller operablyconnected to the analyzer and the clock, the controller configured to:control the analyzer to perform a plurality of HRT measurements over aperiod of time; record measurement values for the plurality of HRTmeasurements in the memory of the implantable medical device; and recorda time with each of the measurement values in the memory of theimplantable medical device.